Systems and methods for opening a tissue

ABSTRACT

Systems and methods for opening a tissue to a target value are disclosed herein. In an exemplary method, a region of the tissue is targeted for opening, a size range of microbubbles corresponding to the target value is determined, microbubbles of the size range are positioned in proximity to the targeted region, and an ultrasound beam is applied to the targeted region such that the tissue is opened with the assistance of the microbubbles to the target value.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. Ser. No. 13/045,070, entitled “Systems And Methods For Opening A Tissue”, filed Mar. 10, 2011; which is a continuation-in-part of International Patent Application No. PCT/US2009/056565 entitled “Systems And Methods For Opening A Tissue”, filed Sep. 10, 2009, which claims priority to U.S. Provisional Application No. 61/095,942 entitled “Molecular Delivery Using Focused Ultrasound”, filed on Sep. 10, 2008, and U.S. patent application Ser. No. 13/045,070 claims priority to U.S. Provisional Application No. 61/377,586 entitled “Effect of Microbubble Size on Fundamental Mode High Frequency Ultrasound Imaging in Mice”, filed Aug. 27, 2010, each of which is incorporated by reference in its entirety herein and from which priority is claimed.

STATEMENT REGARDING FEDERALLY-SPONSORED RESEARCH

This invention was made with government support under R21 EY018505, R01 EB009041, R01-EB009066 and R21-CA139173 awarded by the National Institutes of Health, and CAREER 0644713 awarded by the National Science Foundation. The government has certain rights in the invention.

BACKGROUND

1. Field

The present application relates to systems and methods for opening a tissue utilizing microbubbles.

2. Background Art

The exchange of molecules across the cerebral microvasculature is strictly regulated by a unique interface known as a the blood-brain barrier (BBB). Its primary function is to strictly regulate the brain's environment in order to prevent toxins from entering the parenchyma and maintain molecular environments necessary for proper neuronal firing. The results is the effective exclusion of nearly all systemically administered compounds larger than 400 Da (Daltons) from the brain's extracellular space, rendering many neurologically potent compounds ineffective. So, potential therapeutic agents, such as inhibitors (˜1 kDa) and antibodies (30 to 300 kDa), will not reach their intended targets if administered systemically. Until a method to deliver such large agents in the brain at a critical dose is shown to be effective, advances in the treatment of central nervous system (CNS) disorders will remain impaired.

Focused ultrasound (FUS) applied after the systemic injection of ultrasound contrast agents (UCA) can open the BBB noninvasively. This method can concurrently deliver agents to the brain through the intact skull, locally (to a targeted volume), and transiently with the BBB closing within hours of its opening. In the past, assessment of safety has involved histological analysis to determine the presence of apoptosis, neuronal death, and erythrocyte extravasations, and magnetic resonance imaging (MM) to determine the presence of hemorrhage, macroscopic structural changes, and the timeline of BBB closure. Comprehensive histological analyses of the damage within a few days of sonication has revealed that at specific acoustic parameters (i.e., frequency, pulse length, pulse repetition frequency, and duration) and pressures, BBB opening can occur without widespread hemorrhage or neuronal damage. Other concerns include the presence of small erythrocyte extravasations and the potential of delayed long-term effects that would not be visible in the mostly acute histological evaluations performed. However, the FUS-induced BBB opening results were reproduced in old APP/PS1 Alzheimer's mice where subsequent BBB closure was observed. There is a shortage of effective treatments of CNS diseases and, thereby, a pressing need for a brain drug delivery technique. In light of this need and the lack of clinical options, the safety levels of FUS-induced BBB opening are promising for human applications.

In terms of efficacy, FUS-induced BBB opening can increase the BBB's permeability to therapeutically-relevant-sized agents, such as Omniscan™ (573 Da), Magnevist® (938 Da), Evans Blue, Trypan Blue, Herceptin (148 kDa), doxorubicin (544 Da), and rabbit anti-Aβ antibodies. However, the magnitude of this permeability increase, the spatial distribution of the trans-BBB delivered agents within the targeted volume, and the dependence of both on the molecular weight of the delivered compounds have not been extensively investigated. In order to study these characteristics, dextrans at three distinct molecular weights (3, 70, and 2000 kDa) have been employed as model agents. Although compounds larger than 400 Da can be delivered, a size exclusion threshold remains. For example, a 3 kDa dextran has been delivered more diffusely and at a higher concentration than a 70 kDa dextran. Dextrans have also been deposited at larger amounts proximal to larger vessel branches such as the internal and external transverse hippocampal vessels, and the vessels within the thalamus, when compared to other regions in the targeted hippocampus. As a result, although large compounds can be delivered through the BBB, there remain concerns with the effective concentration and spatial distribution of trans-BBB delivered compounds.

FUS-induced BBB opening studies have used microbubble UCA's (e.g., Definity®, SonoVue®, and Optison™) that were either protein or lipid-shelled with a stabilized gas core. A purpose of these UCA was to provide image contrast while remaining safe for systemic injection by restricting the administered bubble size to below 10 μm. FUS-induced BBB opening, in a stark contrast, involves pre-formed microbubbles to increase the BBB's permeability by opening, for example, the tight junctions or transcellular pathways to allow previously impermeable molecules to go through; in other words, to modulate the biological environment, albeit temporarily. At the low acoustic pressures often used in FUS-induced BBB opening (<1 MPa peak-rarefactional), microbubbles are an important component since opening may not occur without its presence in the vasculature.

Accordingly, there is a need in the art for techniques for opening the BBB in a safe and localized manner.

SUMMARY

Systems and methods for opening a tissue to a target value are disclosed herein. In an exemplary method, a region of the tissue is targeted for opening, a size range of microbubbles corresponding to the target value is determined, microbubbles of the size range are positioned in proximity to the targeted region, and an ultrasound beam is applied to the targeted region such that the tissue is opened with the assistance of the microbubbles to the target value.

The method can include determining a concentration range of microbubbles corresponding to the target value and positioning microbubbles of that concentration range in proximity to the targeted region. The method can also include determining a pressure range for the ultrasound beam corresponding to the target value and applying the ultrasound beam at that pressure range. In some embodiments the pressure range corresponds to a resonance frequency of the microbubbles proximate to the targeted region. The method can further include applying an ultrasound beam to move the microbubbles into vessels of the tissue.

The determination of the size range of microbubbles can include determining a size range corresponding to a size range of vessels the tissue. The size range of microbubbles can be 4 to 5 microns or 1 to 2 microns or 9 to 10 microns or 6 to 8 microns in some embodiments. Further, the microbubbles can be acoustically activated microbubbles and can also be molecule carrying microbubbles. The molecule carrying microbubbles can carry medicinal molecules and/or a contrast agent and/or a biomarker and/or a liposome. Medicinal molecules and/or contrast agents can also be separately positioned in proximity to the targeted region.

A method for imaging the opening of a tissue to a target permeability is also disclosed herein and includes targeting a region of the tissue for opening, determining a size range of microbubbles corresponding to the target value, positioning microbubbles of the size range in proximity to the targeted region, applying an ultrasound beam to the targeted region such that the tissue is opened with the assistance of the microbubbles to the target value, and imaging the targeted region, to form an image of the opened tissue. In some embodiments imaging the targeted region includes applying an ultrasound beam to the targeted region, while in other embodiments imaging the targeted region comprises utilizing a magnetic resonance imaging device to image the targeted region.

An exemplary system for opening a tissue to a target value includes a targeting assembly for targeting a region of the tissue, a solution of size-controlled microbubbles having a size range corresponding to the target value, an introducer for delivering the solution to a location proximate to the targeted region, and a transducer for applying an ultrasound beam to the targeted region thereby opening the tissue with the assistance of the microbubbles to the target value. In some embodiments, the targeting assembly includes an ultrasound transducer and/or at least one member for placement on an anatomical landmark corresponding to the target region.

A system for imaging the opening of a tissue to a target value includes a targeting assembly for targeting a region of the tissue, a solution of size-controlled microbubbles, an introducer for delivering the solution to a location proximate to the targeted region, a transducer for applying an ultrasound beam to the targeted region thereby opening the tissue with the assistance of the microbubbles to the target value, an imaging device for capturing image data of the opened tissue of the targeted region, and a processor for processing the image data to form an image therefrom. In some embodiments, the imaging device includes a transducer, while in other embodiments the imaging device includes a magnetic resonance imaging device.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated and constitute part of this disclosure, illustrate some embodiments of the disclosed subject matter.

FIG. 1 illustrates a method for opening a blood-brain barrier in a brain of a subject to a target permeability in accordance with an exemplary embodiment of the disclosed subject matter.

FIG. 2 illustrates a method for imaging the opening of a blood-brain barrier in a brain of a subject to a target permeability in accordance with an exemplary embodiment of the disclosed subject matter.

FIG. 3(a) illustrates a system for opening and/or imaging the opening of a blood-brain barrier in a brain of a subject to a target permeability in accordance with an exemplary embodiment of the disclosed subject matter.

FIG. 3(b) illustrates another system for opening and/or imaging the opening of a blood-brain barrier in a brain of a subject to a target permeability in accordance with an exemplary embodiment of the disclosed subject matter.

FIGS. 4(a)-(e) illustrate a targeting system for locating a target region of the brain of a subject in accordance with an exemplary embodiment of the disclosed subject matter.

FIG. 5(a) illustrates the size distribution of microbubbles as the number-weighted percentage of the total concentration of bubbles in accordance with an exemplary embodiment of the disclosed subject matter.

FIG. 5(b) illustrates the size distribution of microbubbles as the volume-weighted percentage of the total volume of bubbles in accordance with an exemplary embodiment of the disclosed subject matter.

FIGS. 6(a)-(d) illustrate the increase in average fluorescence of a left brain region of interest relative to a right brain region of interest due to focused ultrasound sonication at different acoustic pressures and microbubble size ranges in accordance with an exemplary embodiment of the disclosed subject matter.

FIG. 6(e) illustrates an increase in average fluorescence of the left brain region of interest relative to the right brain region of interest due to focused ultrasound sonication at 0.61 MPa utilizing 1-2 μm microbubbles in accordance with an exemplary embodiment of the disclosed subject matter.

FIG. 7 illustrates a system for opening the blood-brain barrier used in connection with an experiment on mice in accordance with an exemplary embodiment of the disclosed subject matter.

FIGS. 8(a)-(f) illustrate fluorescence images of three different mouse brains after injection of 1-2 μm microbubbles, sonication at three different acoustic pressures (0.30, 0.46 and 0.61 MPa) and subsequent injection of fluorescent-tagged dextrans of 3 kDa in accordance with an exemplary embodiment of the disclosed subject matter.

FIGS. 9(a)-(h) illustrate fluorescence images of three different mouse brains after injection of 4-5 μm microbubbles, sonication at four different acoustic pressures (0.16, 0.30, 0.46 and 0.61 MPa) and subsequent injection of fluorescent-tagged dextrans of 3 kDa in accordance with an exemplary embodiment of the disclosed subject matter.

FIGS. 10(a)-(f) illustrate histological images of a mouse brain after injection of 1-2 μm microbubbles and focused ultrasound sonication at 0.46 MPa in accordance with an exemplary embodiment of the disclosed subject matter.

FIGS. 11(a)-(f) illustrate histological images of a mouse brain after injection of 4-5 μm bubbles and focused ultrasound sonication at 0.30 MPa in accordance with an exemplary embodiment of the disclosed subject matter.

Throughout the figures and specification the same reference numerals are used to indicate similar features and/or structures.

DETAILED DESCRIPTION

The systems and methods described herein are useful for opening a tissue utilizing microbubbles and focused ultrasound. Although the description is focused on the example of opening the blood-brain barrier, the systems and methods herein are useful for opening other tissues, such as muscular tissue.

The subjected matter disclosed herein are methods and systems for determining size ranges of microbubbles for opening a tissue to allow for the passage of certain molecules over selected areas. Accordingly, the techniques described herein make use of selected size ranges of microbubbles chosen to produce a desired opening effect in a tissue when subjected to focus ultrasound in a selected range of acoustic pressures.

FIG. 1 illustrates a method 100 for opening a tissue to a target value, e.g., a measure of increased ability of the tissue to pass through molecules. The target value can be expressed in terms of an increase in the size of vessels in the tissue, as an area of the tissue that has been opened, or in terms of a rate at which molecules pass through, e.g., a permeability, or as a combination of any of these measures. The method 100 involves targeting 110 a region of the tissue for opening, determining 120 a size range of microbubbles corresponding to the target value, positioning 140 microbubbles of the size range in proximity to the targeted region, and applying 180 an ultrasound beam to the targeted region such that the tissue is opened with the assistance of the microbubbles to the target value.

As illustrated in FIG. 1, in one exemplary embodiment, the method 100 can further include of determining 130 a concentration range of microbubbles corresponding to the target value and the positioning 140 of the microbubbles can also include positioning the microbubbles of the concentration range that corresponds to the target value. The method 100 can also include positioning 150 a contrast agent and/or medicinal molecule (e.g., a drug) in proximity to the target region. In the same or another embodiment, the method 100 can further include determining 160 a pressure range for the ultrasound beam that corresponds to the target value of the tissue and applying 180 the ultrasound beam can include applying the ultrasound beam in the determined pressure range.

In one exemplary embodiment, method 100 can include applying 170 an ultrasound beam to move the microbubbles into vessels of the tissue. This application 170 of the ultrasound beam can be the same, or a different, application 180 that is used to open the tissue. Further, the application 170 of the ultrasound beam can be in the same, or a different, pressure range than that determined 160 for the purposes of opening the tissue.

FIG. 2 illustrates a method 200 in accordance with the disclosed subject matter for imaging the opening of a tissue. The method 200 includes the same basic techniques for opening the tissue to a target value: targeting 110 a region of the tissue for opening, determining 120 a size range of microbubbles corresponding to the target value, positioning 140 microbubbles of the size range in proximity to the targeted region, and applying 180 an ultrasound beam to the targeted region such that the blood-brain barrier is opened with the assistance of the microbubbles to the target value. The method 200 further includes imaging 210 the opened tissue. In some embodiments, imaging 210 the opened tissue can be the same as the application 180 of an ultrasound beam to open the tissue. In another embodiment, imaging 210 can include utilizing an Mill device to image the opening of the tissue.

FIG. 3(a) illustrates a system 300 for opening a tissue to a target value. System 300 has many of the same features as the system described in U.S. Patent Pub. No. 2009/0005711, a commonly assigned patent application which is incorporated by reference in its entirety herein. Ultrasound waves are generated by a focused ultrasound transducer (FUS) 302, which can be a single-element circular-aperture FUS transducer. In one exemplary embodiment the FUS transducer 302 can be a single-element, spherical segment FUS transducer with center frequency of 1.525 MHz, a focal depth of 90 mm, an outer radius of 30 mm, and an inner radius of 11.2 mm (Riverside Research Institute, New York, N.Y., USA). The FUS transducer can be provided with hole in its center for receipt of an imaging transducer 304, which can be a single-element diagnostic transducer having a center frequency of 7.5 MHz with a focal length of 60 mm (Riverside Research Institute, New York, N.Y., USA). The FUS transducer 302 and the diagnostic transducer 304 can be positioned so that the foci of the two transducers are properly aligned, e.g., overlap.

Further illustrated in FIG. 3(a), an exemplary system 300 can include a cone 306 filled with degassed and distilled water and mounted on system 300. The cone 306 can, for example, be manufactured from a clear plastic, such as polyurethane. The water is contained in the cone 306 by capping it with a material considered substantially “transparent” to the ultrasound beam, such as an ultrathin polyurethane membrane 308 (Trojan; Church & Dwight Co., Princeton, N.J., USA).

The transducer assembly, which can include the FUS transducer 302 and the diagnostic transducer 304, can be mounted to a computer-controlled 3-D positioning system 310 (Velmex Inc., Lachine, QC, Canada), including motors VXM-1 and VXM-2 used in the exemplary embodiment. It is understood that other positioning systems can be incorporated for positioning the transducer assembly with respect to the targeted tissue.

In the same or another exemplary embodiment, the FUS transducer 302 can be driven by a function generator 320, e.g., function generator HP33150A, manufactured by Agilent Technologies, Palo Alto, Calif., USA, through an amplifier 322, such as a 50-dB power amplifier 3100L (ENI, Inc., Rochester, N.Y., USA). The diagnostic transducer 304 can be driven by a pulser-receiver system 342, for example a pulser-receiver 5052PR (Panametrics, Waltham, Mass., USA), connected to a digitizer 326, e.g., digitizer CS14200 (Gage Applied Technologies, Inc., Lachine, QC, Canada). It is understood that the above-described components can be modified or replaced with other components, as is known in the art, for producing the ultrasound beams described herein. Computer 328 typically includes a processor, such as a CPU (not shown), and can be any appropriate personal computer or distributed computer system including a server and a client. For example, a computer useful for this system is a Dell Precision 380 personal computer. It is understood that any personal computer, laptop, or other processor that can load software and communicate with the various components discussed herein can be used. A memory unit (not shown), such as a disk drive, flash memory, volatile memory, etc., can be used to store software for positioning and operating the transducer assembly, image data, a user interface software, and any other software which can be loaded onto the CPU.

In another exemplary embodiment illustrated in FIG. 3(b), system 300′ can include a transducer assembly having an array of a plurality of single-element FUS transducer 304 and 305 which can be targeted to different regions of the brain of the subject. Each FUS transducer 304, 305 in the array can be fired individually, thereby permitting opening of the BBB in several locations without repositioning the transducer assembly.

Prior to sonication and in order to verify undistorted propagation through the skull, a scan, such as a 3-D raster-scan (lateral step size: 0.2 mm; axial step size: 1.0 mm), of the beam of the FUS transducer 302, can optionally be performed in a large water tank containing degassed water with a needle hydrophone having a needle diameter on the order of about 0.2 mm (Precision Acoustics Ltd., Dorchester, Dorset, UK). In this manner the pressure amplitudes and three-dimensional beam dimensions of the FUS transducer 302 can be measured. The pressure amplitudes can be measured by calculating the peak-rarefactional pressure values and accounting for an pressure attenuation due to transcranial propagation, e.g., an 18% pressure attenuation. The dimensions of the beam provided by the FUS transmitter 302 can have a lateral and axial full-width at half-maximum (FWHM) intensity of approximately 1.32 and 13.0 mm, respectively, and in some embodiments can be approximately equal to the dimensions of the beam after propagation through the skull.

System 300 also includes a liquid container 334 containing an appropriate liquid 336, e.g., degassed and distilled water, which is sealed at the bottom with a membrane 338, which can be a polyurethane membrane that is acoustically and transparent, e.g., plastic wrap. The system 300 can also include an optical imaging device 340, such as a digital camera, for imaging the skull of the subject 332 and a MRI device 350 for imaging the brain of the subject 332.

System 300 also includes a platform 330 for the subject. In one exemplary embodiment, the platform 330 for the subject can be a polyurethane bed for a smaller subject 332, such as a mouse. In this configuration, the membrane 338 can be placed over the subject 332. In other embodiments, the platform 330 can be a hospital bed or surgical table, in which a larger subject 332 (such as a human subject) can be laid prone or supine and the transducer assembly positioned on top of the region of the skull targeted.

Additional components of the system 300 include a targeting system 400, coupled to the FUS transducer 302, for locating the focus of the FUS transducer 302 in the brain of the subject 332. The targeting system 400 can be coupled by any known method that permits the targeting system 400 to aid in properly targeting the FUS transducer 302 to the region of interest for opening of the target tissue, e.g., acoustic and/or optical coupling. FIGS. 4(a)-(d) illustrate a targeting system 400 for use with an embodiment where the subject 332 is a mouse. FIG. 4(a) illustrates mouse skull 401, where the skull's sutures can be seen through the skin and used as anatomic landmarks for targeting purposes. As illustrated in FIG. 4(a), the landmarks of mouse skull 401 include the sagittal suture 402, the frontal bone 404, the interparietal bone 406, the left parietal bone 408, and the right parietal bone 410.

FIG. 4(b) illustrates the placement of targeting system 400 on skull 401 in accordance with an exemplary embodiment. The targeting system 400 can include a plurality of members 420, 422, 424, such as thin metal bars, e.g., 0.3 mm thin metal bars, fabricated from an acoustically reflective material, e.g., paper clips. The metal bars 420, 422, 424 can be placed on several landmarks of the skull of the subject to create a layout, or grid. As illustrated in FIG. 4(b), a grid consisting of three equally spaced 0.3-mm thin F2 metal bars 420, 422, 424 was placed in the water bath 334 on top of the skull 401 and in alignment with these landmarks, e.g., bone sutures. The first bar 420 was aligned parallel and along the sagittal suture 402, and the second bar 424 was attached perpendicularly to the first bar and in alignment with the suture between the parietal 408 and interparietal bone 406. The third bar 422 was placed 4 mm away from and parallel to the second bar 424.

FIG. 4(c) illustrates the location of a brain structure 440 to be targeted, here the hippocampus, relative to the landmarks noted above. The location of the hippocampi are assumed relative to the sutures based on the mouse brain and known skull anatomy. In this exemplary embodiment, using the grid positioning system 400, the location of one of the hippocampi (indicated by circle 440) was reproducibly targeted when assumed to be at mid-distance (arrow 442) between the parallel bars 422, 424 and 2 mm away from the center bar 420 (arrow 444).

To locate the desired brain structure 440 an image, such as a lateral 2-D raster scan, of the grid configuration can be made using the diagnostic transducer 304. The focus of the FUS transducer 302 can then be positioned to precisely target the desired brain structure 440. In another exemplary embodiment, the targeting system can include other imaging devices, such as a digital camera 340. For example, a digital camera 340 can be used to photograph the head of the subject 332. The relevant landmarks can be identified in the photograph, and the focus of the FUS transducer 302 targeted to a location relative to the landmarks. In addition, other MRI targeting equipment, as is known in the art, can be used for targeting the desired brain structure 440 or other targeted tissue structure.

FIG. 4(d) illustrates the actual location of the hippocampus 446 as indicated in the histology slice. FIG. 4(e) illustrates a lateral 2-D raster-scan 490 of the grid 400 using the diagnostic transducer 304. The location of the hippocampus can be identified relative to this grid. The focus of the FUS transducer 302 was placed 3 mm beneath the top of the skull by measuring distance with the diagnostic transducer 304. Using the grid positioning system 400 and depth calculations, precise, accurate and reproducible targeting of the hippocampus or other brain structures can be performed. In one exemplary embodiment, the grid positioning system 400 allowed for sonication of the same location with good accuracy across different mice. This allowed for not only good reproducibility across different mice, but also a good comparison of BBB opening effects in different regions 440 within the sonicated area.

An exemplary method 100 for opening the BBB will be described in connection with the above-referenced figures. The subject 332 is positioned on a platform 330. Subject 332 can be positioned in a prone position, and can be anesthetized for the sonication procedure. The degassed and distilled water bath 334 is suspended over the subject's 332 head. Ultrasound gel can be used to reduce any remaining impedance mismatches between the thin plastic layer 338 and the subject's 332 skin. The transducer assembly can be placed in the water bath 334 with its beam axis perpendicular to the surface of the skull 401.

The focus of the transducer is positioned inside the subject's 332 brain. The focus can be targeted 110 to a region of the brain 440, such as the desired brain tissue, e.g., the hippocampus 446, or to the vasculature of the brain, e.g., arteries, ventricles, arterioles, and capillaries of the brain, or to other target tissue regions at different locations in the subject 332. The targeted region 440 of the brain can be located 110 utilizing the targeting system as discussed above.

Determination and production of the appropriate size and concentration ranges of microbubbles will now be described in connection with an exemplary embodiment. The appropriate size range of microbubbles can be determined 120 by comparing the bubble size to the cerebral vasculature size and selecting a bubble size that is small enough to perfuse the vessels while at the same time large enough to induce sufficient mechanical stress on the vessel walls, such that the vessels are opened to the target value.

The target value of the tissue can be selected based on the size of the molecule that is to pass through the tissue, e.g., the BBB, or based on the size, e.g., area, of the region that is to be exposed to the molecule, or a combination of the two. In one exemplary embodiment, microbubbles of 4-5 μm were determined 120 to be an appropriate size range for opening the BBB of mice to a target value which allowed for the passage of 3 kDa molecules into an area on the order of 2 mm. In another exemplary embodiment, 1-2 μm bubbles were determined 120 to be an appropriate size range for opening the BBB of mice to a target value which allowed for the passage of 3 kDa molecules in an area on the order of 1 mm. In other embodiments, size-isolated microbubbles in the range of 6-8 μm and/or 9-10 μm can be determined 120 to be an appropriate size range for opening the BBB. In one exemplary embodiment, the target value can be such that molecules up to the megaDalton size range are able to pass through the BBB, e.g., 2 MDa molecules.

In one exemplary embodiment, microbubbles including of a 1,2-Distearoyl-sn-glycero-3-phosphocholine (DSPC) and polyoxyethylene-40 stearate (PEG40S) lipid-shell and a perfluorobutane (PFB) gas core can be manufactured. In other exemplary embodiments, the microbubbles can be any type of microbubbles that capable of being acoustically activated, e.g., vibrated, such that they induce mechanical stress on the interior of a tissue vessel wall. Size-selected microbubbles can be isolated from a polydispersed microbubble distribution using a method described in International Patent Application No. PCT/US09/56513, a commonly assigned patent application which is incorporated by reference herein in its entirety. In brief, this method utilizes a two part procedure: acoustic emulsification and differential centrifugation.

Acoustic emulsification was used to generate a polydispersed microbubble distribution. A mixture of DSPC and PEG40S in filtered PBS was heated and its lipid aggregates were dispersed into smaller unilamellar liposomes by sonicating with a 20-kHz probe (Model 250A, Branson Ultrasonics; Danbury Conn., USA) at 3 W. PFB gas was then flowed over the surface of the lipid suspension. Microbubbles were then generated by sonicating the suspension at 33 W for about 10 s at the gas-liquid interface and collected in 30-mL syringes (Tyco Healthcare, Mansfield, Mass.). Subsequent washing and size fractionation was performed with a bucket-rotor centrifuge (Model 5804, Eppendorf, Westbury, N.Y.; radius: 16 cm from the center to the syringe tip; RPM: 10 to 14500 RPM). Microbubbles from the suspension were collected as a cake (portion of the centrifuged syringe located substantially radially inward) after centrifuging at 300 RCF for 10 min.

Differential centrifugation was used to isolate microbubbles of select 1-2, 4-5, or 6-8 μm diameter ranges. In each case, the initial microbubble size distribution of the cake was measured by laser light obscuration and scattering (Accusizer 780A, NICOMP Particle Sizing Systems, Santa Barbara, Calif.) to determine the relative centrifugal force (RCF) necessary for a microbubble size range to rise in the syringe column. Stokes' equation was used for the rise velocity of a buoyant particle relative to the bulk fluid under creeping flow conditions. Based on this equation, bubble suspensions were centrifuged at a specific RCF and duration whereby its resulting cake, or infranatant (portion of the centrifuged syringe located radially outward) was re-suspended to preserve either larger or smaller bubbles, respectively. The centrifugation and re-suspension process was repeated several times until the desired 1-2, 4-5, or 6-8 μm diameter range were obtained. The final cake was re-dispersed to a 1-mL volume of 20 vol % glycerol solution in PBS and stored in a 2-mL serum vial with PFB headspace.

In one example, 1-2 μm bubbles were isolated from an initial microbubble sample collected in 60 mL syringes. Microbubbles greater than 6 μm were removed by centrifuging the initial microbubble suspension at 50 RCF for 1 min. The infranatant containing smaller bubbles was re-suspended to 60 mL with PBS, while the cake containing larger bubbles was discarded. Microbubbles greater than 3 μm diameter were removed by centrifuging the collected infranatant at 290 RCF for 1 min. The infranatant was re-suspended to 60 mL with PBS, while the cake was discarded. The collected infranatant was concentrated down to 1 mL using 300 RCF for 5 min. The sample was stored in 2-mL serum vials. The final gas concentration of the suspension was at least 1 vol % to ensure stability.

Microbubbles in the 4-5 μm size range were isolated by first centrifuging the initial microbubble sample at 120 RCF for 1 min to remove bubbles less than 4 μm in diameter. The resulting cake was collected and reconstituted with PBS, while the infranatant was discarded. This washing step was repeated five to seven times to fully remove smaller bubbles from the sample. Microbubbles greater than 6 μm were removed by centrifuging the resulting suspension at 80 RCF for 1 min. The infranatant containing 4-5 μm bubbles was collected, while the cake was discarded. The infranatant was re-suspended and centrifuged at 80 RCF for 1 min again to completely remove the larger bubbles. This size-isolation procedure was repeated two to three times to collect a sufficient number of microbubbles. The resulting cakes containing 4-5 μm bubbles were combined and concentrated to 1 mL. The final gas concentration of the 4-5 μm microbubble suspension ranged from 2-5 vol %.

Microbubbles in the 6-8 μm size range were isolated by first centrifuging the initial sample at 60 RCF for 1 min to remove bubbles smaller than 6 μm. The cake was collected and reconstituted with PBS, while the infranatant was discarded. This washing step was repeated five to seven times to fully remove smaller bubbles from the sample. Microbubbles greater than 8 μm in diameter were removed by centrifuging the resulting suspension at 40 RCF for 1 min. The infranatant containing 6-8 μm bubbles was collected, while the cake was discarded. The infranatant was re-suspended and centrifuged at 40 RCF for 1 min to completely remove the larger bubbles. The size-isolation procedure was repeated two to three times to produce enough 6-8 μm bubbles for storage. The resulting cakes containing 6-8 μm bubbles were combined and concentrated to 1 mL. The final gas concentration of the 6-8 μm microbubble suspension ranged from 2-10 vol %.

The final microbubble size distribution in each vial was verified by laser light obscuration and scattering (Accusizer 780A, NICOMP Particle Sizing Systems, Santa Barbara, Calif.) before and after its use in the FUS-induced BBB opening experiments.

In one exemplary embodiment, it was shown that sonication of systemically administered 140 lipid-shelled bubbles isolated in separate diameter ranges of 1-2 and 4-5 μm can induce BBB opening in mice. It was further found that the pressure threshold for inducing BBB opening was lower in the presence of the 4-5 μm bubbles compared to the 1-2 μm bubbles. In fact, the fluorescence from trans-BBB delivered dextrans was greater for larger bubbles at every pressure amplitude tested. Apart from bubble size dependence, BBB opening was shown to be dependent on the brain region sonicated. Greater fluorescence was observed in the thalamus when compared to the hippocampus. Furthermore, preliminary histological evaluation indicated that custom, in-house manufactured, discrete size-isolated bubbles were not inducing any discrete damage sites at pressure amplitudes around the discovered threshold.

Thus, it was shown that in-house manufactured, discrete size-isolated bubbles with a 1,2-Distearoyl-sn-glycero-3-phosphocholine (DSPC) and polyoxyethylene-40 stearate (PEG40S) shell and a perfluorobutane (PFB) gas core can induce BBB opening, adding to the group of pre-formed microbubbles capable of opening the BBB (e.g., in addition to Definity®, SonoVue®, and Optison™). Differential centrifugation, discussed above, was a key procedure, since it allowed for the production of large volumes of discrete size-isolated bubbles.

A typical size distribution for 1-2 μm and 4-5 μm diameter bubbles used in accordance with an exemplary embodiment, are depicted in FIG. 5(a) as the number-weighted and in FIG. 5(b) as the volume-weighted percentage of the total number of bubbles and gas volume, respectively. The solid lines in FIGS. 5(a)-(b) illustrate the size distribution of the two bubble size ranges prior to the BBB experiment, discussed further below, and the dashed lines indicate the distribution of size after the BBB experiment. As illustrated, in both instances, there was minimal size overlap between the two sets of bubbles. In the experiment discussed below, in order to test for stability, size distribution measurements were acquired from the same vial before the BBB opening and between 6 and 11 hours after the BBB opening experiments.

Table 1 illustrates the number-weighted and volume-weighted mean and median bubble sizes and polydispersity index (PI) for both sets of discrete size-isolated microbubbles. The PI, which was defined as the volume-weighted mean diameter divided by the number-weighted mean diameter, can be calculated to assess size uniformity. The 1-2 μm bubbles had number-weighted and volume-weighted mean and median diameters within the 1-2 μm range and a good PI value of 1.2±0.1 before the BBB opening experiments. After the experiment, the PI increased to 2.1±0.9, as indicated by the increased discrepancy between number-weighted and volume-weighted mean diameters. However, this distribution remained distinct in the 4-5 μm bubble set.

The 4-5 μm bubbles had volume-weighted mean and median values within the 4-5 μm range and a good PI value of 1.5±0.1. The number-weighted diameters were below the 4 μm target lower limit, but were still deemed distinct from the 1-2 μm bubble set. The volume-weighted diameter mean and median of the 4-5 μm range were 5.0±0.2 and 4.3±0.1, respectively. The bubble size distribution did not significantly change after the BBB opening experiments as indicated by the PI value of 1.4±0.1.

The stability of commercially available microbubbles have previously been characterized as stable over a period of at least two days. As illustrated in Table 1, the in-house manufactured bubbles discussed herein had a greater change in the Polydispersity Index (PI) over less than a day, but this could have been due to the fact that a large volume of bubbles were extracted from the vial with too little remaining for proper size distribution measurement with an Accusizer measurement device. As a result, after taking into account this potential artifact, the bubble's mean and median diameters did not necessarily change from before to after the BBB opening experiments as Table 1 seems to suggest. Regardless, even in the case where Table 1 indicated the actual maximum change in bubble diameter, the isolated peaks of bubbles remained distinct from one another, as illustrated in FIGS. 5(a) and 5(b).

TABLE 1 Summary of Microbubble Size Distribution Number-weighted diameter Volume-weighted diameter (μm) (μm) (Mean ± SD) (Median ± SD) (Mean ± SD) (Median ± SD) PI 1-2 μm bubbles Before experiment 1.2 ± 0.1 1.2 ± 0.1 1.5 ± 0.2 1.5 ± 0.1 1.3 ± 0.1 After experiment 1.4 ± 0.2 1.3 ± 0.1 2.9 ± 1.5 2.6 ± 1.5 2.1 ± 0.9 4-5 μm bubbles Before experiment 3.3 ± 0.1 3.4 ± 0.1 5.0 ± 0.2 4.3 ± 0.1 1.5 ± 0.1 After experiment 3.2 ± 0.2 3.2 ± 0.2 4.6 ± 0.4 4.3 ± 0.2 1.4 ± 0.1

The appropriate concentration of microbubbles can be determined 130 based on the nature of the subject 332, e.g., a human or a mouse, based on the size of the target region 440, e.g., the surface area of the BBB that one wishes to open, and based on the vessel size in the target region 440, e.g., 4-8 μm, or a combination of these factors. In the example of opening a BBB area on the order of millimeters, a concentration range of 10⁷ to 10⁹ bubbles/mL can be appropriate. In one exemplary embodiment, the total concentration for both size ranges of bubbles, e.g., 1-2 and 4-5 μm, was kept constant at approximately 8.5×10⁸ number of bubbles per mL. In order to ensure accuracy of concentration, the bubbles were generated at an initial yield larger than the desired concentration and then diluted in PBS one minute before intravenous injection into the mouse.

In one exemplary embodiment, the bubble concentration can be chosen to be the same across different size distributions as opposed to the volume fraction, because it was assumed that BBB opening occurred discretely, e.g., the sites of molecular leakage highly correlated with the instantaneous locations of the bubbles at the time of sonication. This implied that BBB opening sites punctuated along the length of the capillaries. In the case where the volume fraction was kept the same for both sets of bubbles, it is deemed that the imaging protocol used would have the required sensitivity to detect minute increases in fluorescence.

FIGS. 6(a)-(d) illustrate the increase in average fluorescence of the left region of interest (ROI) relative to the right ROI (the control) due to FUS sonication at different acoustic pressures and microbubble size ranges, in accordance with an exemplary experiment discussed below. FIGS. 6(a) and 6(b) illustrate the results where the hippocampi was the ROI and FIGS. 6(c) and 6(d) illustrate the results where the thalami was the ROI. FIGS. 6(a) and 6(c) illustrate the results using the 1-2 μm bubbles, while FIGS. 6(b) and 6(d) illustrate the results using the 4-5 μm bubbles. As illustrated in FIGS. 6(a) and 6(c), at 0.30 MPa, no increase in fluorescence in any of the mouse brains studied was detected. Although the overall concentration could have no effect on whether BBB opening occurs, it can have an effect on the number of BBB opening sites along the capillary length, and thus the amount of fluorescent-tagged dextrans infusing the parenchyma, e.g., the permeability. This can be a possible factor contributing to the 4-5 μm bubbles having greater fluorescence than 1-2 μm bubbles at a given pressure amplitude, as illustrated in FIGS. 6(b) and 6(d).

In one exemplary embodiment, the solution of microbubbles can be inserted 140 into the subject 332 such that the microbubbles make their way to the BBB of the subject 332. In one exemplary embodiment involving mice, a 25 μl bolus of the microbubble solution was injected 140 into the tail vein of the mouse 1 minute prior to sonication. In the example of a tissue that is outside the body of a subject 332, the solution of microbubbles can be position 140 in proximity to the target region by use of a syringe, or other appropriate device.

Following sonication, as described herein, the BBB opens, thereby facilitating the passage of a molecule through the BBB. Thus, a solution of contrast agent and/or other molecules (e.g., drugs) can be inserted 150 into the subject 332 such that it makes its way to the BBB and is able to pass through the same upon the opening of the BBB. The insertion 150 of the molecule into the subject 332 can occur prior to sonication, during sonication, or following sonication. Such molecule can be a drug, medication or pharmaceutical compound, protein, antibody or biological material, chemical substance, contrast agent, or any other material to pass through the BBB. In some embodiments, the molecule, whether a contrast agent, drug or other molecule, can be contained within a microbubble. In the same or another embodiment, the molecule can itself be composed of a microbubble. Further the molecule can be contained inside the microbubbles of the solution that is used to open the BBB or can itself be the same microbubbles. Such molecule can be inserted 150 into the subject 332 by any known method. For example, the molecule can be injected 150 into a vein of the subject. The molecule can also be administered 150 intraperitoneally by a catheter. In some embodiments, the molecule can be administered 150 orally. In the example of a tissue that is outside the body of a subject 332, the molecules can be positioned 150 in proximity to the target region by use of a syringe, or other appropriate device.

In some embodiments, an ultrasound can be applied 210 to image the opening of the BBB. For example, an ultrasound contrast agent can be administered 150 to the subject 332. Ultrasound scans 210 of the subject can be used to determine whether the BBB has opened. A bolus of ultrasound contrast agent, e.g., Optison™ containing microbubbles, can be injected into a vein of the subject 332 prior to sonication. In an exemplary embodiment, a 10 μL bolus (approximately 0.4 mL/kg) of Optison™ containing microbubbles having a mean diameter: 3.0 to 4.5 μm and a concentration of 5.0 to 8.0×10⁸ bubbles per mL can be injected into the right femoral vein of the subject 332 fifteen minutes prior to sonication. High-resolution echocardiogram equipment can be used following sonication to determine the presence of the ultrasound contrast agent. Microbubbles containing material such as a contrast agent or a drug are administered to the subject 332 for traversal of the BBB.

An MRI contrast agent can also be administered 150 to the subject 332 for passage through the BBB. MM scans can be used to monitor opening of the BBB. As illustrated in FIG. 3(a), in order to facilitate MRI scans during the procedure, an MM system 350 can be incorporated into the equipment described hereinabove. T1- and T2-weighted MRI scans can be obtained using a 1.5 T, 3.0 T, 9.4 T, or other, system (Bruker Medical; Boston, Mass. USA). For example, 0.5 mL of MRI contrast agent gadolinium (Omniscan; Amersham Health, AS Oslo, Norway) can be administered 150 intraperitoneally via a catheter to depict BBB opening. Intraperitoneal injection 150 allows for the slow uptake of the Mill contrast agent into the bloodstream. After injection 150 of the MM contrast agent, a series of scans 210 can be performed on the subject 332. For example, six alternating T1-weighted and T2-weighted fast spin-echo image scans 210, using the following specifications: a repetition time/echo time (TR/TE) of 4000 ms/9.2 ms; rapid acquisition with relaxation enhancement: 16; field of view (FOV) of 1.92×1.92 cm; matrix size of 256×256; number of slices: 10; slice thickness: 0.6 mm; slice gap: 0.1 mm; number of excitations (NEX): 10, 15 and 45.

Contrast-enhanced behavior can be followed for a period of time after injection 150 of the contrast agent, to assess the time course of BBB opening. Detection of BBB opening can be detected (imaged) 210 by comparing an area of a nonsonicated homogeneous brain region with sonicated regions. Increased pixel intensity values of the sonicated regions which are increased above the values of the nonsonicated regions by a predetermined value, e.g., 2.5 standard deviations, are determined to be a contrast-enhanced region, revealing BBB opening. Higher resolution analysis can be used over an extended time period to determine the path of deposition of the molecule through the BBB.

The FUS transducer 302 supplies the focused ultrasonic waves to the targeted region 440. For example, pulsed-wave FUS can be applied in a series of bursts having delays between bursts. In an exemplary embodiment, the burst rate is about 1 to 20 Hz, the burst duration is 0.1 to 20 ms, and the duty cycle is 5-20%.

In some embodiments, the FUS acoustic pressure to be applied can be determined 160 based on size of the microbubbles compared to the size of the vessels in the target region 440 of the BBB such that the target value of opening is achieved. Exemplary acoustic pressures at the focus can be 0.15 to 3.0 MPa. In one example where the target value was such that 3 kDa molecules entered across an area on the order of 2 mm and utilizing 4-5 μm microbubbles at a concentration of 8.5×10⁸ bubbles/mL, a pressure of 0.61 MPa was sufficient to acquire this target value. Other pressures fall within the range of 0.15-0.9 MPa. According to one embodiment, the FUS was applied in a series of five shots lasting, e.g., 10-40 ms each, with a delay between each shot of about 10-40 seconds. The FUS sonication procedure can be performed once or more on the subject's 332 brain. The actual output acoustic pressure values of the FUS transducer 302 can be calculated experimentally, for example, obtained from the values found in degassed water and corrected using the attenuation values of a skull similar to the subject's skull 401. Thus the FUS transducer 302 can be set at the proper level to produce the determined 160 pressure at the target region 440 of the subject's 332 brain.

In one example involving mice and as illustrated in FIGS. 6(a)-(d), the lowest peak-rarefactional pressure necessary for inducing BBB opening was 0.46 MPa for the 1-2 μm bubbles and 0.30 MPa for the 4-5 μm bubbles. The acoustic pressure threshold of BBB opening can be defined as the lowest pressure necessary for inducing BBB opening. Even though at 0.61 MPa there was significant BBB opening with the 1-2 μm bubbles, the fact that BBB opening was observed at 0.46 MPa for at least one mouse indicates that BBB opening can occur at this pressure amplitude. Thus in this exemplary embodiment, the acoustic pressure threshold for BBB opening fell between 0.30 and 0.46 MPa for the 1-2 μm bubbles and between 0.15 and 0.30 MPa for the 4-5 μm bubbles.

The rationale for the above-noted difference in acoustic pressure threshold can be based on the fact that cavitation and fragmentation threshold of microbubbles increases with decreasing vessel size. Changes in the bubble's resonance frequency and/or its constraint within a microvessel can be a factor in the increase in cavitation and fragmentation thresholds of microbubbles located in smaller vessels. It has previously been shown that commercially, non-size-isolated microbubbles are delivered both homogeneously across the BBB and concentrated near or along large vessels walls. However, when a small bubble (1-2 μm) flows in a capillary, it is not as constrained as a large bubble within that same environment. If the mechanical stress from the bubble against the vessel wall is the primary cause for BBB opening, then a high acoustic pressure amplitude will be necessary to induce this effect. Larger bubbles, given their comparable size (4-5 μm) to the capillary diameter (4-8 μm), can have higher inertial cavitation and fragmentation thresholds and persistence than if they were not as constrained by the vessel wall. Applying a low acoustic pressure to a bubble approximately the size of the microvessel can initiate stable bubble oscillations that induce stress against the wall as the bubble increases in size to fill the vessel. This mechanical stress can be high enough at 0.30 MPa to induce BBB opening for the 4-5 μm bubbles.

Accordingly, for bubbles that are not of a comparable size to the target region's vessels a higher pressure is necessary to induce the same degree of opening of the BBB. Thus, it is particularly advantageous to determine 120 the proper size range of microbubbles and to insert 140 a solution of discrete size-isolated microbubbles within the determined size range, as opposed to a solution of microbubbles that are not size-isolated, e.g., currently available polydispersed microbubbles.

FIG. 6(e) illustrates the increase in average fluorescence of the left ROI relative to the right ROI due to FUS sonication at 0.61 MPa utilizing 1-2 μm bubbles. As illustrated in FIG. 6(e), the thalamus exhibits greater fluorescence, e.g., BBB opening, than the hippocampus. This could be due to the capillary density and/or the vascular architecture of the thalamus compared to the hippocampus. The higher number of capillaries, or sites of potential BBB opening, can be the cause for increased permeation of agents. Another possible rationale for the difference in fluorescence could be due to the fact that the extracellular space varies in terms of structure and diffusion rate, which implies differences in the rate of travel of delivered agents once they exit the vascular system.

Example

FIG. 7 illustrates a system 300 used in an experiment, approved by the Columbia University Institutional Animal Care and Use Committee, on twenty-eight wild-type mice (strain: C57BL/6, mass: 28.0±4.5 g, sex: male; Harlan, Indianapolis, Ind., USA) which were studied in accordance with the techniques described herein. As illustrated in FIG. 7, the system 300 can include a FUS transducer 302, a pulse-echo diagnostic transducer 304, a cone 306, a latex membrane 308, a 3-D positioning system 310 all operatively connected to a function generator 320, a power amplifier 322, a pulse-receiver system 324, a digitizer 326 and a computer 327. The cone 306 can be inserted into a water container 334 which is sealed at the bottom by a polyurethane membrane 338 and placed on the shaved skull 702 of the mouse subject 332. The mouse subject 332 is held in place using a stereotaxic apparatus 704.

In the experiment, the mice were anesthetized using 1.25-2.50% isoflurane (SurgiVet, Smiths Medical PM, Inc., Wisconsin, USA) throughout both the BBB opening and transcardial perfusion procedures. After being anesthetized, each mouse 332 was placed prone with its head immobilized by the stereotaxic apparatus 704 (David Kopf Instruments, Tujunga, Calif., USA). The hair on the skull was removed using an electric trimmer and a depiatory cream. A degassed water-filled container 334 sealed at the bottom with thin, acoustically and optically transparent, Saran™ Wrap 338 (Saran™; SC Johnson, Racine, Wis., USA) was placed on top of the mouse head 702 while ultrasound coupling gel was used to eliminate any remaining impedance mismatch between the two surfaces. The FUS transducer 302 was then submerged in the water of the container 334 with its beam axis perpendicular to the surface of the skull 332.

The focus of the transducer was positioned inside the mouse brain using a grid-positioning method that utilized the pulse-echo diagnostic transducer 304, as discussed above. The grid was constructed from three 0.30 mm thin metal bars (i.e., paper clips) with two of the bars parallel to one another and separated by 4.00 mm. At the center of the parallel bars, and perpendicular to the two, was soldered the third bar. The grid was placed in the water bath 334, on top of the skull, and in alignment with sutures visible through the skin. The center bar was aligned along the sagittal suture and one of the parallel bars with the lambdoid suture. A lateral two-dimensional raster-scan of the grid using the diagnostic transducer was made and the transducer's beam axis was positioned 2.25 and 2.00 mm away from the sagittal and lambdoid suture, respectively. Finally, the focal point was placed 3.00 mm beneath the top of the skull so that the acoustic wave propagated through the left parietal bone and overlapped with the left hippocampus and a small portion of the lateral region of the thalamus. The right hippocampus was not targeted and was used as the control. The grid positioning method was sufficiently precise to have the FUS beam consistently overlap the hippocampus of the murine brain.

A 25 μl bolus of either the 1-2 or 4-5 μm diameter bubbles was injected into the tail vein 1 minute prior to sonication. For the 1-2 bubble set, pulsed FUS (pulse rate: 10 Hz, pulse duration: 20 ms, duty cycle: 20%) was applied at a set pressure of 0.30, 0.46, or 0.61 MPa peak-rarefactional in a series of two intervals consisting of 30-s of sonication at a single location (e.g., the hippocampus). Between each interval, a 30-s window allowed for residual heat between pulses to dissipate and microbubbles to reperfuse the cerebral vasculature undisturbed by the acoustic wave. The experiment was repeated for the 4-5 μm bubble set, but acoustic pressures were set at 0.15, 0.30, 0.46, or 0.61 MPa peak-rarefactional. The pressure ranges designated for the different bubble sets were roughly based on previous work with commercially available, non-size-isolated Definity® microbubbles. Since previous work has shown that the vascular characteristics (e.g., vascular density) in the sonicated region can influence the extent of BBB opening, the FUS sonication procedure was performed once and at a single location in each mouse brain in order to more accurately compare BBB opening pressure thresholds.

Approximately 10 min after FUS-induced BBB opening, 3 kDa Texas Red®-tagged dextrans were injected via the femoral vein. After a 20-min interval, which enabled the dextrans to circulate throughout the vasculature, the mice were transcardially perfused with 30 ml of phosphate buffer saline (138 mM sodium chloride, 10 mM phosphate, pH 7.4) and 60 ml of 4% paraformaldehyde. The brain was extracted from the skull and then post-fixed in paraformaldehyde overnight. Following the aforementioned procedures, the brain was prepared for either frozen (m=22) or paraffin sections (n=6). The frozen sectioning protocol provided an efficient means of analyzing fluorescence in order to determine the threshold for BBB opening. Meanwhile, the paraffin sections were used to analyze not only the presence of trans-BBB delivered dextrans, but also to assess for damage when sonicating at the pressure thresholds, e.g., 0.46 MPa with the 1-2 μm bubbles and 0.30 MPa with the 4-5 μm bubbles.

In preparation of frozen sectioning, the brain was cryoprotected by soaking it in 30% sucrose overnight. The brain was then embedded in a cutting temperature compound (Sakura Tissue-Tek O.C.T. Compound; Torrance, Calif., USA), frozen in a square mold, and then sectioned using a cryostat into 200 μm slices in the horizontal orientation. In preparation for paraffin sectioning the brain was embedded in paraffin. From the dorsal side of the brain, 1.2 mm was trimmed away. At the first level, 6 sections at 6 μm were obtained and placed on 3 slides. Then 80 μm were bypassed until the next level was sectioned. This was repeated for 12 levels for a total of 72 sections. At each level, the first two sections were stained with hematoxylin and eosin (H&E) while the latter four remained unstained and left for fluorescence imaging to detect the trans-BBB delivered dextrans.

Bright field and fluorescent images of the frozen sections were acquired using an inverted light and fluorescence microscope (IX-81; Olympus, Melville, N.Y., USA) at 4× magnification and with a motorized stage-scanner. Images of the paraffin sections were acquired using an upright light and fluorescence microscope (BX61; Olympus, Melville, N.Y., USA) at 4× and 10× magnification. In both cases, the Texas Red-tagged dextrans were excited at 568±24 nm while emissions were filtered for 610±40 nm.

In the case of the frozen sections, horizontal sections were chosen at defined cross-sections of the hippocampus, as depicted in FIGS. 8(a)-(f) (the 1-2 μm bubbles) and FIGS. 9(a)-(h) (the 4-5 μm bubbles). As illustrated in FIGS. 8 and 9, a 3×3 mm² region of interest (ROI) in the bright field images was selected using Adobe® Photoshop® CS2 (San Jose, Calif., USA) and the hippocampus and thalamus were manually outlined within this ROI. The outlines were then loaded into MATLAB® 2007 (Natick, Mass., USA) and used to isolate the hippocampus in the fluorescent images. The relative increase in fluorescence was then calculated by subtracting the spatially averaged fluorescence in the right ROI from the spatially averaged fluorescence in the left ROI and then dividing the resulting value by the spatially averaged fluorescence in the right ROI.

Differences between two sets of values were determined using statistical analysis. Following the calculation of the mean and standard deviation in the change of fluorescence of the left over the right hippocampus for the five sets of values, a Students's t-test was performed. The same comparison amongst the five sets of values for the increase in area of fluorescence was made. In all comparisons, a difference in fluorescence at P<0.05 was considered statistically significant (FIGS. 6(a)-(d)).

As noted above, FIGS. 8(a)-(f) illustrate fluorescence images of three different mouse brains after injection of 1-2 μm bubbles, sonication at three different acoustic pressures (0.30, 0.46 and 0.61 MPa) and subsequent injection of fluorescent-tagged dextrans of 3 kDa. FIGS. 8(a), 8(c) and 8(e) (the left ROI) illustrate the left hippocampus and thalamus which were FUS sonicated, while FIGS. 8(b), 8(d) and 8(f) illustrate the right hippocampus and thalamus which were not sonicated (the right ROI).

As illustrated in FIGS. 8(a)-(f), following the systemic injection of 1-2 μm bubbles, FUS sonication induced an increase in fluorescence at 0.46 and 0.61 MPa (FIGS. 8(a), 8(c)) while no fluorescence increase was observed at 0.30 Mpa (FIG. 8(e)). At 0.46 MPa, increased fluorescence was predominant in the hippocampal fissure and the fissure between the hippocampus and thalamus. However, fluorescence in these regions was not included in the outline of either the hippocampus or thalamus since they do not have extensive capillary networks and are situated near large vessels. Although increases in fluorescence were observed in regions with a more homogeneous distribution of capillaries (i.e., no large vessels), it was not consistent across enough mice to unequivocally indicate BBB opening and resulted in a wide variation in the increase in fluorescence (P>0.1; FIG. 6(a), (b)). However, a statistically significant increase was observed at 0.61 MPa, as illustrated in FIGS. 6(a) and 6(b).

As noted above, FIGS. 9(a)-(h) illustrate fluorescence images of three different mouse brains after injection of 4-5 μm bubbles, sonication at four different acoustic pressures (0.16, 0.30, 0.46 and 0.61 MPa) and subsequent injection of fluorescent-tagged dextrans of 3 kDa. FIGS. 9(a), 9(c), 9(e) and 9(g) (the left ROI) illustrate the left hippocampus and thalamus which were FUS sonicated, while FIGS. 9(b), 9(d), 9(f) and 9(h) illustrate the right hippocampus and thalamus which were not sonicated (the right ROI).

As illustrated in FIGS. 9(a)-(h), following the systemic injection of 4-5 μm bubbles, FUS sonication induced an increase in fluorescence at 0.30, 0.46 and 0.61 MPa (FIGS. 9(a), (c), and (e)) that were statistically significant (P<0.05) while no fluorescence increase was observed at 0.15 MPa (FIG. 9(g)). At 0.30 MPa and above, fluorescence was observed not only at the fissures and along large vessels, but diffusely through the hippocampus and thalamus. A statistically significant increase in fluorescence in the hippocampus was detected between 0.30 and 0.46 MPa.

For each ROI and acoustic pressure, 4-5 μm bubbles produced greater increases in fluorescence compared to the 1-2 μm bubbles. In addition, the peak negative pressure amplitude threshold where significant fluorescence was observed was lower for the 4-5 μm bubbles than for the 1-2 μm bubbles. This implies that a lower acoustic pressure is required to induce BBB opening for the larger 4-5 μm bubbles.

It was qualitatively noted that there were regional variations in fluorescence within the sonicated region (FIGS. 8(a), (c)). Therefore a comparison of the enhancement in fluorescence in the thalamus and hippocampus at 0.61 MPa and with 1-2 μm bubbles was performed. As illustrated in FIG. 6(e), a clear difference in the increase in fluorescence was detected (P<0.01).

Six mouse brains were assessed for histological damage as defined by the presence of discrete damage sites, such as neuronal damage (dark neurons), gross hemorrhage, vacuolization, and small erythrocyte extravasations. Three of the six mice were sonicated at 0.46 MPa in the presence of 1-2 μm bubbles while the other three were sonicated at 0.30 MPa in the presence of 4-5 μm bubbles. No discrete sites of hemorrhage were detected in the twelve slices analyzed at level sections 1, 6, 8, 10, and 12.

FIGS. 10(a)-(f) illustrate histological images of a mouse brain after injection of 1-2 μm bubbles and sonicated at 0.46 MPa (6-μm thick fluorescent unstained and H&E-stained slices that were sequentially sectioned), with FIGS. 10(a), 10(c) and 10(e) illustrating the left hippocampal and thalamic regions which were sonicated and FIGS. 10(b), 10(d) and 10(f) illustrating the right hippocampal and thalamic regions which were not sonicated. FUS sonication in the presence of 1-2 μm bubbles clearly depicts BBB opening at 0.46 MPa, as illustrated by comparing FIG. 10(a) with 10(b). The sections directly above those depicted in FIGS. 10(a) and 10(b) were H&E-stained and are illustrated in FIGS. 10(c) and 10(d), which are 4× magnifications. FIGS. 10(e) and 10(f) are 10× magnifications which illustrate the ROI's indicated by the black boxes in FIGS. 10(c) and 10(d). As can be seen in FIGS. 10(c)-(f), no discrete damage sites were observed. In some sections (FIG. 10(e)), erythrocytes were qualitatively observed (small white arrows), but they also appeared in the control, contralateral hemisphere (FIG. 10(f)), thus indicating that this might be due to histological artifacts rather than damage cause by the FUS sonication. In addition, it was difficult to determine whether these erythrocytes remained within vessels or whether they had extravasated.

FIGS. 11(a)-(f) illustrate histological images of a mouse brain after injection of 4-5 μm bubbles and sonicated at 0.30 MPa (6-μm thick fluorescent unstained and H&E-stained slices that were sequentially sectioned), with FIGS. 11(a), 11(c) and 11(e) illustrating the left hippocampal and thalamic regions which were sonicated and FIGS. 11(b), 11(d) and 11(f) illustrating the right hippocampal and thalamic regions which were not sonicated. FUS sonication at 0.30 MPa in the presence of 4-5 μm bubbles also resulted in BBB opening, as illustrated by comparing FIG. 11(a) with 11(b). As with the 1-2 μm range depicted in FIGS. 10(c) and 10(d), the 4-5 μm range illustrated in FIGS. 11(c) and 11(d) (at 4× magnification and H&E-stained) shows no discrete damage sites due to the FUS sonication. Small erythrocyte extravasations were observed (as indicated by white arrows) on both the sonicated and control hemispheres, as illustrated in FIGS. 11(e) and 11(f) (at 10× magnification of the black box ROI's in FIGS. 10(c), (d)).

As FIGS. 10(e), 10(f), 11(e) and 11(f) illustrate, for the respective minimum pressures and bubbles tested, regions where a high intensity of fluorescence was observed were not associated with any dead neurons, necrotic sites, or hemorrhaging, thus confirming the safety and efficacy of using discrete size-isolated microbubbles to effectuate the opening of the blood-brain barrier as discussed herein.

It will be understood that the foregoing is only illustrative of the principles described herein, and that various modifications can be made by those skilled in the art without departing from the scope and spirit of the disclosed subject matter. For example, the system and methods described herein are used for opening the blood-brain barrier of a subject. It is understood that that techniques described herein are useful for opening of any vascular tissue. Further, the techniques described have been performed on mice but it is understood the techniques are applicable to other subject, such as humans. Moreover, features of embodiments described herein can be combined and/or rearranged to create new embodiments. 

1. A method for opening a tissue to a target value, comprising: targeting a region of the tissue for opening; selecting the target value based on a size of a molecule to pass through the tissue and a surface area of the region to be exposed to the molecule; determining a size range of microbubbles corresponding to the target value; positioning the microbubbles of the size range in proximity to the targeted region; determining a pressure range of an ultrasound beam corresponding to the size range of the microbubbles and the target value; and applying the ultrasound beam at the pressure range to the targeted region such that the tissue is opened with the assistance of the microbubbles to the target value.
 2. The method of claim 1, further comprising determining a concentration range of microbubbles corresponding to the target value, and wherein positioning the microbubbles further comprises positioning the microbubbles of the concentration range.
 3. The method of claim 1, wherein the pressure range corresponds to a resonance frequency of the microbubbles proximate to the targeted region.
 4. The method of claim 1, wherein positioning the microbubbles comprises applying the ultrasound beam at a first pressure range to move the microbubbles into vessels of the tissue.
 5. The method of claim 4, wherein the pressure range corresponding to the size range of the microbubbles and the target value comprises a second pressure range different from the first pressure range.
 6. The method of claim 1, wherein the tissue comprises a blood-brain barrier.
 7. The method of claim 1, wherein the tissue comprises a vessel.
 8. The method of claim 1, wherein determining the size range of microbubbles comprises determining a size range corresponding to a size range of vessels of the tissue.
 9. The method of claim 1, wherein the size range of microbubbles is 4 to 5 microns.
 10. The method of claim 1, wherein the size range of microbubbles is 1 to 2 microns.
 11. The method of claim 1, wherein the size range of microbubbles is 9 to 10 microns.
 12. The method of claim 1, wherein the size range of microbubbles is 6 to 8 microns.
 13. The method of claim 1, wherein the microbubbles are acoustically activated microbubbles.
 14. The method of claim 1, wherein the microbubbles are molecule carrying microbubbles.
 15. The method of claim 14, wherein the molecule is a medicinal molecule.
 16. The method of claim 14, wherein the molecule is a contrast agent.
 17. The method of claim 14, wherein the molecule is a biomarker.
 18. The method of claim 14, wherein the molecule is a liposome.
 19. The method of claim 14, wherein the molecule carrying microbubbles are carrying a medicinal molecule and a contrast agent.
 20. The method of claim 1, further comprising positioning medicinal molecules in proximity to the targeted region.
 21. The method of claim 1, further comprising positioning a contrast agent in proximity to the targeted region.
 22. The method of claim 1, further comprising collecting image information for the targeted region of the opening tissue.
 23. The method of claim 22, wherein imaging the targeted region comprises applying an ultrasound beam to the targeted region.
 24. The method of claim 22, wherein imaging the targeted region comprises utilizing a magnetic resonance imaging device to image the targeted region.
 25. A system for opening a tissue to a target value, comprising: a targeting assembly for targeting a region of the tissue; a processor programmed with logic configured to: determine a size range of microbubbles corresponding to the target value; and determining a pressure range of an ultrasound beam corresponding to the size range of the microbubbles and the target value; an introducer adapted to deliver a solution including the microbubbles of the size range to a location proximate to the targeted region; and a transducer, coupled to the targeting assembly, adapted to apply the ultrasound beam to the targeted region to thereby open the tissue with the assistance of the microbubbles to the target value.
 26. The system of claim 25, wherein the targeting assembly comprises one or more members for placement on an anatomical landmark of the tissue.
 27. The system of claim 25, wherein the solution of size-controlled microbubbles further comprises a microbubble concentration range corresponding to the target value.
 28. The system of claim 25, wherein the solution of size-controlled microbubbles further comprise microbubbles of a size range corresponding to a size range of vessels of the tissue.
 29. The system of claim 25, wherein the pressure range corresponds to a resonance frequency of the microbubbles proximate to the targeted region.
 30. The system of claim 25, wherein the transducer is adapted to position the microbubbles by applying the ultrasound beam at a first pressure range to move the microbubbles into vessels of the tissue.
 31. The system of claim 30, wherein the pressure range corresponding to the size range of the microbubbles and the target value comprises a second pressure range different from the first pressure range.
 32. The system of claim 25, wherein the tissue comprises a blood-brain barrier.
 33. The system of claim 25, wherein the tissue comprises a vessel.
 34. The system of claim 25, wherein the size range of microbubbles is 4 to 5 microns.
 35. The system of claim 25, wherein the size range of microbubbles is 1 to 2 microns.
 36. The system of claim 25, wherein the size range of microbubbles is 9 to 10 microns.
 37. The system of claim 25, wherein the size range of microbubbles is 6 to 8 microns.
 38. The system of claim 25, wherein the microbubbles are acoustically activated microbubbles.
 39. The system of claim 25, wherein the microbubbles are molecule carrying microbubbles.
 40. The system of claim 39, wherein the molecule is a medicinal molecule.
 41. The system of claim 39, wherein the molecule is a contrast agent.
 42. The system of claim 39, wherein the molecule is a biomarker.
 43. The system of claim 39, wherein the molecule is a liposome.
 44. The system of claim 25, further comprising a solution of medicinal molecules and an introducer for delivering the solution of medicinal molecules to a location proximate to the targeted region.
 45. The system of claim 25, further comprising a solution of contrast agent and an introducer for delivering the solution of contrast to a location proximate to the targeted region.
 46. The system of claim 25, further comprising: an imaging device adapted to capture image data of the opened tissue of the targeted region; and an image processor, operatively coupled to the imaging device, adapted to process the image data to form an image therefrom.
 47. The system of claim 45, wherein the imaging device comprises an imaging ultrasound transducer.
 48. The system of claim 45, wherein the imaging device comprises a magnetic resonance imaging device. 